JP2008200097A - Ultrasonograph and data processing method - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To support users in setting trace lines. <P>SOLUTION: A continuous tomogram 72 is an image sequentially displaying tomograms of a plurality of cross-sections. The tomogram includes a placenta 42B, a uterus 43, and an amniotic fluid 45 contacting the placenta. Furthermore, a manual trace line 66 set by a user is also displayed. The outline of the placenta 42B some times become obscure in its boundary with the uterus 43. The sequential display of the tomograms of a plurality of cross-sections arranged on the basis of a representative cross-section by the continuous tomogram 72 permits a subtle image variation in the vicinity of the boundary of the placenta 42B, a subtle difference in the tendency of a speckle to occur or disappear outside and inside the boundary for example, to be sensuously read. Consequently, even in the part where the boundary between the placenta 42B and the uterus 43 is obscure, the user can comparatively precisely find the boundary. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to an ultrasonic diagnostic apparatus and a data processing method, and more particularly to a technique for setting a trace line corresponding to a contour of a target tissue.

  A three-dimensional space (three-dimensional echo data capturing space) can be formed by scanning a scanning plane formed by scanning an ultrasonic beam in a direction orthogonal thereto. Conventionally, the Disk Summation method is well known as a method of extracting a target tissue existing in a three-dimensional space and calculating its volume. In this conventional method, each of a plurality of slice data aligned across the target tissue is displayed as a tomographic image, and the contour of the target tissue is manually traced on each tomographic image, whereby a cross-sectional area is obtained for each slice data. I want. The element volume of the target tissue portion is calculated using the cross-sectional area and thickness (cross-sectional interval) for each slice data. The volume of the target tissue is obtained by adding the element volumes.

  Patent Document 1 describes a process for extracting a tissue (such as a heart chamber) existing in a three-dimensional space. Patent Document 2 describes that a tissue is extracted using a contour model. Patent Document 3 describes a technique for correcting a manual trace result. Patent Documents 4 and 5 describe techniques for calculating the volume of tissue.

  Further, in Patent Document 6, an original image of a target tissue before contour extraction and an image (contour extraction image) in which a contour is extracted and superimposed on the target tissue are alternately displayed and extracted. A technique is described that can easily determine whether or not the contour is correct. However, the technique is based on the premise that a contour extraction image is generated by superimposing a contour extracted by some method on the target tissue, and extracted using the original image and the contour extraction image in which the image information of the target tissue matches. It is determined whether or not the contour is correct. However, when the contour of the target tissue is unclear, it is difficult to extract the contour in the first place, and it is difficult to determine whether the contour is correct or not by simply switching between these two images. is there.

  It is desirable to reduce the burden on the user while maintaining high accuracy when specifying or measuring the target tissue. However, in any of the above documents, there are a mixture of parts with unclear tissue contours and clear parts. In this case, a configuration for exhibiting the advantages of manual tracing and automatic tracing is not described. For example, regarding the placenta in the uterus in the second trimester of pregnancy, the luminance difference between the uterus is small in the area around the placenta and in contact with the uterus, and the luminance difference between the amniotic fluid and the area in contact with the amniotic fluid is small. large. In such a situation, there is a demand for improving the accuracy of the trace while reducing the burden on the user when tracing the outline of the placenta.

Japanese Patent Laid-Open No. 2004-159997 JP 2002-224116 A JP-A-11-164834 Japanese Patent Laid-Open No. 10-305033 JP 2002-330968 A JP-A-10-105678

  By the way, when the outline of the target tissue is manually traced on the tomographic image, it is difficult to trace a portion where the outline is unclear. Alternatively, a burden imposed on the user for tracing is large for a portion with an unclear outline. Therefore, it is desirable to support such unclear portions so that manual tracing can be performed as accurately as possible or in a short time. Such a request is the same when manual tracing is performed on all spatially arranged tomographic images and when manual tracing is performed only on a plurality of representative tomographic images in consideration of the burden on the user. Can be pointed out.

  In such a situation, the inventor of the present application has conducted research and development on an improved technique related to setting a trace line corresponding to the contour of the target tissue. We paid particular attention to the accuracy of tracing and the burden on users for tracing.

  The present invention has been made in the course of research and development, and an object thereof is to provide a technique for assisting a user in setting a trace line.

  In order to achieve the above object, an ultrasonic diagnostic apparatus according to a preferred aspect of the present invention includes a data acquisition unit that obtains volume data by transmitting and receiving ultrasonic waves to and from a three-dimensional space including a target tissue, and a volume Within a virtual data space composed of data, a cross-section setting unit for setting a cross-section set composed of a plurality of cross-sections for the target tissue, and a representative cross-section included in the cross-section set from the user A trace processing unit that sets a manual trace line corresponding to the contour of the target tissue according to the input, and a plurality of cross-sectional slices arranged on the basis of the representative cross-section in the cross-section set as an input support image for the input And a display processing unit that sequentially displays images.

  According to the above aspect, a cross section set including a plurality of cross sections is set for the target tissue in the data space. In this case, it is desirable to set the cross-section set so that the entire target tissue is covered. Further, the interval between individual sections in the section set may be equal or non-uniform. For example, the cross-sectional density may be increased for a site where the shape of the target tissue greatly changes. When the cross section set is set, at least one desirably a plurality of representative cross sections are determined, and a manual trace line is set on each representative cross section. Since manual tracing is not performed on all the cross sections, but manual tracing is performed on the representative cross section, the burden on the user can be reduced.

  Furthermore, in the above aspect, tomographic images of a plurality of cross sections arranged on the basis of the representative cross section are sequentially displayed as an input support image for the user when performing manual tracing. When the outline of the target tissue (boundary with other tissues) is very unclear on the representative cross section, it is difficult to recognize the outline even if only one image of the representative cross section is continuously stared. In contrast, in the above aspect, the tomographic images of a plurality of cross sections arranged with reference to the representative cross section are sequentially displayed, so that subtle image changes near the boundary of the target tissue, for example, occurrence of speckle inside and outside the boundary, It becomes possible to read sensuously that the tendency of disappearance is slightly different. That is, it is possible to find the boundary of the target tissue with relatively high accuracy even in a portion where the boundary of the target tissue is unclear from the comprehensive determination using the tomographic images of a plurality of cross sections. Moreover, since the input support image is displayed by the display processing unit, for example, an operation of searching for a plurality of cross sections around the representative cross section or an operation of sequentially displaying the plurality of cross sections can be omitted. That is, it is possible to perform manual tracing with high accuracy while reducing the burden imposed on the user.

  In a preferred aspect, the display processing unit synthesizes and displays the image of the manual trace line in a tomographic image sequentially displayed as the input support image.

  In a preferred aspect, the display processing unit displays a reference image representing an arrangement state of a plurality of cross sections constituting the cross section set, and sets a marker for specifying the position of the cross section currently displayed in the input support image. It is characterized by being displayed in a reference image.

  In a desirable mode, the display processing unit displays a marker indicating an array range of a plurality of cross sections used in the input support image in the reference image.

  In a preferred aspect, an array range of a plurality of slices used for the input support image and a display speed of tomographic images sequentially displayed as the input support image are variably set.

  In order to achieve the above object, a data processing method according to a preferred aspect of the present invention is a method for processing volume data obtained by transmitting and receiving ultrasonic waves to and from a three-dimensional space including a target tissue. In a virtual data space composed of volume data, for a target tissue, a section setting step for setting a section set composed of a plurality of sections, and a representative section included in the section set, A trace processing step for setting a manual trace line corresponding to the contour of the target tissue in response to an input from the user, and an input support image for the input, a plurality of arrays arranged with reference to a representative cross section in the cross section set And a display processing step for sequentially displaying cross-sectional tomographic images.

  The data processing method of the above aspect is executed by, for example, an ultrasonic diagnostic apparatus or a computer. When the computer executes, for example, a program for causing the computer to execute each step of the data processing method is used. That is, when the computer reads the program, the computer executes the data processing method.

  The present invention provides a technique for assisting a user in setting a trace line. For example, according to a preferred aspect of the present invention, an input support image is displayed, and manual tracing can be performed with high accuracy while reducing a burden imposed on the user.

  DESCRIPTION OF EXEMPLARY EMBODIMENTS Hereinafter, preferred embodiments of the invention will be described with reference to the drawings.

  FIG. 1 is a block diagram showing the overall configuration of an ultrasonic diagnostic apparatus according to the present invention. This ultrasonic diagnostic apparatus is used in the medical field, and in particular has a function of extracting a target tissue in a living body and calculating its volume. Examples of the target tissue include placenta, malignant tumor, gallbladder, thyroid and the like. In the following description, a process for extracting a placenta as a target tissue is shown.

  In FIG. 1, a 3D probe 10 is an ultrasonic transducer that is used, for example, in contact with a body surface or inserted into a body cavity. In this embodiment, the 3D probe 10 has a 2D array transducer. The 2D array transducer is composed of a plurality of vibration elements aligned in the first direction and the second direction. An ultrasonic beam is formed by the 2D array transducer, and the ultrasonic beam is two-dimensionally scanned. As a result, a three-dimensional echo data capturing space is formed as a three-dimensional space. Specifically, the three-dimensional space is configured as an aggregate of a plurality of scanning planes, and each scanning plane is configured by one-dimensional scanning with an ultrasonic beam. Instead of the 2D array transducer, a 3D space similar to the above can be formed by mechanically scanning the 1D array transducer.

  The transmission unit 12 functions as a transmission beam former. The transmitter 12 supplies a plurality of transmission signals to the 2D array transducer with a predetermined delay relationship. As a result, a transmission beam is formed. The reflected wave from the living body is received by the 2D array transducer, and a plurality of reception signals are output from the 2D array transducer to the receiving unit 14. The receiving unit 14 performs a phasing addition process on the plurality of reception signals, and thereby outputs a reception signal (beam data) after the phasing addition. Predetermined signal processing is performed on the received signal, for example, detection, logarithmic conversion processing, and the like are performed, and beam data that is the received signal after signal processing is stored in the 3D data memory 16.

  The 3D data memory 16 has a three-dimensional storage space similar to a three-dimensional space that is a transmission / reception space in a living body. When writing to or reading from the 3D data memory 16, coordinate conversion is performed on each data. In the present embodiment, when writing to the 3D data memory 16, coordinate conversion from the transmission / reception coordinate system to the storage space coordinate system is executed. This constitutes volume data as will be described later. Volume data is an aggregate of a plurality of frame data (slice data) corresponding to a plurality of scanning planes, and each frame data is composed of a plurality of beam data. Each beam data consists of a plurality of echo data arranged in the depth direction. Incidentally, each configuration after the 3D data memory 16 can be configured as dedicated hardware, or can be realized as a function of software such as a computer.

  The three-dimensional image forming unit 18 executes image processing based on, for example, a volume rendering method based on the volume data stored in the 3D data memory 16, thereby forming a three-dimensional ultrasonic image (image data). The image data is sent to the display image forming unit 26. The arbitrary tomographic image forming unit 20 forms a tomographic image (image data) corresponding to an arbitrary cross section in the three-dimensional space set by the user. In that case, a data array corresponding to an arbitrary cross section in the 3D data memory 16 is read, and a B-mode image as an arbitrary tomographic image is formed based on the data array. The image data is sent to the display image forming unit 26.

  The tissue extraction unit 22 is a module that executes image data processing unique to the present embodiment, which will be described in detail below, and extracts a target tissue (or target tissue data) existing in a three-dimensional space or volume data by a trace process. To do. In this case, manual tracing and automatic tracing are used together, and automatic correction processing for each trace result is applied. These will be described in detail later. The extracted target tissue data is sent to the display image forming unit 26 and used for image display of the target tissue. In addition, the extracted target tissue data is sent to the volume calculation unit 24 in this embodiment.

  The volume calculation unit 24 is a module that calculates the volume of the target tissue by the volume calculation method described above, for example, the disk summation method. That is, since the tissue extraction unit 22 forms a plurality of trace lines as a closed loop over the entire target tissue, the volume of the target tissue is approximately obtained based on the trace lines. In that case, the distance between each closed loop, that is, between each cross section is also used. The calculated volume value data is sent to the display image forming unit 26. The volume calculation unit 24 may obtain the volume of the target tissue by the Average Rotation method or the like.

  Each of the modules such as the three-dimensional image forming unit 18, the arbitrary tomographic image forming unit 20, and the tissue extracting unit 22 functions according to the operation mode selected by the user, and the display image forming unit 26 has each mode. Corresponding data is input. The display image forming unit 26 performs processing such as image composition processing and coloring processing on the input data, and outputs the resulting data to the display unit 28. The display unit 28 displays a three-dimensional ultrasonic image, an arbitrary tomographic image, a three-dimensional image of the extracted tissue, a volume value, and the like according to the selected operation mode. Incidentally, it is also possible to synthesize and display a 3D image of the entire 3D space and a 3D image of the target tissue.

  The control unit 30 controls the operation of each component shown in FIG. 1, and controls the operations of the tissue extraction process and the volume calculation described above, particularly based on parameters set by the user by the input unit 32. . In addition, the control unit 30 is responsible for controlling data writing to the 3D data memory 16. The input unit 32 is configured by an operation panel having a keyboard, a trackball, and the like. The control unit 30 is configured by a CPU, an operation program, and the like. A single CPU may execute 3D image processing, arbitrary tomographic image formation processing, tissue extraction processing, and volume calculation.

  Next, the target tissue extraction processing will be specifically described with reference to FIGS. FIG. 2 is a flowchart showing the entire process.

  In S101 of FIG. 2, data is collected using the 3D probe described above. In this case, a plurality of scanning planes are formed. The observation target (target tissue) in the present embodiment is, for example, the placenta. In S102, volume data is constructed on the 3D data memory shown in FIG. In S103 of FIG. 2, the reference cross section is set by appropriately adjusting the position of the cross section while displaying the arbitrary tomographic image on the display unit.

  FIG. 3 shows a reference cross section 46 set for the placenta (placenta data) 42 in the volume data (three-dimensional data space) 44. In this case, it is desirable to position the reference cross section 46 so that the entire placenta 42, which is the target tissue, appears as a cross section, in particular, so that this cross section is maximized. However, as will be described later, a reference cross-section row (cross-section set) is set as a cross-section set, and therefore the reference cross-section 46 is set so that the reference cross-section row covers the entire placenta 42 that is the target tissue. Is sufficient.

  In S104 of FIG. 2, as shown in FIG. 4, on the tomographic image 46 </ b> A corresponding to the reference cross section, points on both ends of the placenta 42 </ b> B that is the target tissue are set by the user. The points at both ends are represented by reference numerals 50 and 52 in FIG. A straight line connecting them is a reference line 54. In FIG. 4, the code | symbol 43 has shown the uterus and the code | symbol 45 has shown amniotic fluid. As shown in the figure, the placenta 42B is joined to the inner wall of the uterus 43, and on the tomographic image 46A, the joined portion, that is, the boundary portion has a small luminance difference and the boundary is unclear. In S104 of FIG. 2, the number m of the cross sections constituting the reference cross section row described below is set.

  When the reference line 54 is set, as shown in FIG. 5, a reference section row 56 is automatically generated for the three-dimensional data space constituted by the volume data 44. The reference cross-section row 56 is configured as a plurality of cross sections orthogonal to the reference line 54 shown in FIG. 4, that is, it arranges a plurality of cross sections at regular intervals or non-uniform intervals from one point 50 to the other point 52. It corresponds to a thing. The reference section row 56 shown in FIG. 5 includes a plurality of manual trace reference sections 58 and a plurality of automatic trace reference sections 60. Here, the reference cross section 58 for manual tracing is formed in a predetermined number, and the number is n. For example, the value of n is determined within a range of 5 to 10. The reference cross section for manual tracing here corresponds to a representative cross section, and manual tracing is performed only for the representative cross section, so that the burden on the user can be greatly reduced. On the other hand, as will be described later, automatic tracing is executed by interpolation processing for each automatic tracing reference section 60.

  More specifically, in S105 of FIG. 2, the selected n reference cross sections are displayed as a tomographic image on the screen. For example, tomographic images corresponding to each of the n reference cross sections 58 shown in FIG. 5 are arranged in one screen and displayed simultaneously. One tomographic image corresponding to each of the n reference sections 58 may be displayed one by one.

  In S106 of FIG. 2, manual trace processing is executed for each tomographic image, that is, the outline of the placenta, that is, the boundary is traced by the user while observing the image using the input unit. The trace result is shown in FIG. Reference numeral 42B represents a cross-section of the placenta, and reference numeral 42C represents the outline of the placenta. The outline has a portion that is indistinct by contacting the uterus 43 and a portion that is relatively clear by contacting the amniotic fluid 45. Reference numeral 66 represents a manual trace line, and a contour 42C is traced as a closed loop. The manual trace line 66 has a uterus 43 side portion 66B and an amniotic fluid 45 side portion 66A.

  In particular, in the portion 66B on the uterus 43 side, the boundary is unclear due to a small luminance difference between the uterus 43 and the placenta 42B. Even if it is an indistinct portion, it is possible to trace to some extent by human visual judgment, but this is not always easy. Therefore, in the present embodiment, a continuous tomographic image is formed as an input support image and displayed on the display unit in order to support the manual trace operation by the user.

  FIG. 7 shows a display image example 1 displayed during manual tracing. The display image 70 shown in FIG. 7 is suitable when, for example, the Disk Summation method is used. The display image 70 is formed in the display image forming part (reference numeral 26 in FIG. 1) and displayed on the display part (reference numeral 28 in FIG. 1). The display image 70 includes a continuous tomographic image 72 that functions as an input support image and an index image 74 that functions as a reference image.

  The continuous tomographic image 72 is an image that sequentially displays tomographic images of a plurality of cross sections arranged with reference to the representative cross section in the cross section set. That is, one of the n manual trace reference cross sections (representative cross sections) 58 shown in FIG. 5 is selected, and the selected manual trace reference cross section 58 and a plurality of automatic traces arranged in the vicinity thereof are used. A plurality of tomographic images corresponding to the reference cross section 60 are sequentially displayed. As shown in FIG. 7, the tomographic images sequentially displayed include the placenta 42B and the uterus 43 and amniotic fluid 45 in contact therewith. Further, a manual trace line 66 set by the user is also displayed.

  The outline of the placenta 42 </ b> B, which is the target tissue, may be blurred particularly at the boundary with the uterus 43. If it is unclear, it is difficult to recognize the contour even if the user continues to stare at only one image of the representative cross section. On the other hand, in the present embodiment, since the tomographic images of a plurality of cross sections arranged with the representative cross section as a reference are sequentially displayed by the continuous tomographic image 72, a subtle image change near the boundary of the placenta 42B, for example, the boundary It becomes possible to sensuously read the difference in the tendency of speckle generation and disappearance inside and outside. That is, it is possible to find the boundary between the placenta 42B and the uterus 43 with comparatively high accuracy even in a portion where the boundary between the placenta 42B and the uterus 43 is unclear, based on comprehensive judgment using tomographic images of a plurality of cross sections. Further, since the continuous tomographic image 72 is formed by the display image forming unit, for example, an operation of searching for a plurality of cross sections around the representative cross section or an operation of sequentially displaying the plurality of cross sections can be omitted. That is, the user can perform manual tracing with high accuracy while reducing the burden imposed on the user while viewing the continuous tomographic image 72.

  Furthermore, in the present embodiment, the index image 74 is formed by the display image forming unit. The index image 74 is an image representing an arrangement state of a plurality of cross sections constituting the cross section set. That is, the arrangement state of a plurality of reference section rows (reference numeral 56 in FIG. 5) set for the placenta 42 is displayed. In the index image 74, all m reference cross-section columns may be displayed, but only the manual trace reference cross-section (representative cross-section) may be displayed. In FIG. 7, an array state of eight representative cross sections from A to H is displayed in the index image 74. Of the eight representative cross sections from A to H, only the representative cross section C that is currently subject to manual tracing is highlighted with a solid line, and the other representative cross sections are displayed with broken lines.

  In the index image 74, a marker indicating the array range of a plurality of cross sections used in the continuous tomographic image 72 is displayed. That is, in FIG. 7, filled triangular markers are displayed at the positions of the representative cross section B and the representative cross section D. This indicates that a continuous tomographic image 72 is formed by using a cross section existing between the representative cross section B and the representative cross section D. Incidentally, the continuous tomographic image 72 may be obtained by sequentially displaying a plurality of cross sections from the representative cross section B to the representative cross section D, and conversely, a plurality of cross sections from the representative cross section D to the representative cross section B. May be displayed sequentially. Of course, a plurality of cross sections may be reciprocally displayed between the representative cross section B and the representative cross section D.

  Further, in the index image 74, a marker for specifying the position of the cross section currently displayed in the continuous tomographic image 72 is displayed. That is, in FIG. 7, a white triangular marker is displayed in the vicinity of the representative cross section C. This shows that the cross section corresponding to the position of this marker is currently displayed in the continuous tomographic image 72. As the cross sections are sequentially displayed, the white triangular markers are represented by the representative cross section B and the representative cross section D. Is displayed moving between.

  It should be noted that the arrangement range of a plurality of cross sections used in the continuous tomographic image 72, that is, the positions of the filled triangular markers, the display speed of the cross sections sequentially displayed as the continuous tomographic images 72, that is, the white triangle markers. It is desirable that the moving speed is variably set according to, for example, a user operation.

  Further, when displaying the continuous tomographic image 72, the cross section to be manually traced may be continuously displayed by a watermark display process or the like. For example, when manual tracing of the representative cross section C in FIG. 7 is performed, the image of the representative cross section C is continuously displayed with a luminance of 50% as the continuous tomographic image 72, and the representative cross section B is displayed on the image of the representative cross section C. Tomographic images of a plurality of cross sections from the representative cross section D to the representative cross section D may be superimposed and displayed sequentially with 50% luminance. As a result, it is possible to form a continuous tomographic image 72 in which a plurality of cross-sections are sequentially displayed while the image of the representative cross-section C is left in the watermark process.

  FIG. 8 shows a display image example 2 displayed during manual tracing. A display image 70 ′ illustrated in FIG. 8 is suitable when, for example, the Average Rotation method is used. As with the display image 70 shown in FIG. 7, the display image 70 ′ shown in FIG. . The display image 70 ′ includes a continuous tomographic image 72 that functions as an input support image and an index image 74 ′ that functions as a reference image. Note that the continuous tomographic image 72 is the same as that described above (FIG. 7), and a description thereof will be omitted here.

  The index image 74 ′ is an image that represents an arrangement state of a plurality of cross sections constituting the cross section set. That is, the arrangement state of a plurality of reference section rows set for the placenta 42 is displayed. In the Average Rotation method, a plurality of reference section rows are arranged so as to rotate a plane around a single axis. In the index image 74 ′, all reference cross-section rows may be displayed, but only the manual cross-section reference cross-section (representative cross-section) may be displayed. In FIG. 8, in the index image 74 ′, the arrangement state of six representative cross sections from A to F is displayed. Of the six representative cross sections from A to F, only the representative cross section C that is currently subject to manual tracing is highlighted with a solid line, and the other representative cross sections are displayed with broken lines.

  In the index image 74 ′, a marker indicating the array range of a plurality of cross sections used in the continuous tomographic image 72 is displayed. That is, in FIG. 8, filled triangular markers are displayed at the positions of the representative cross section B and the representative cross section D. This indicates that a continuous tomographic image 72 is formed by using a cross section existing between the representative cross section B and the representative cross section D. In the index image 74 ′, a marker for specifying the position of the currently displayed cross section in the continuous tomographic image 72 is displayed. That is, in FIG. 8, a white triangular marker is displayed in the vicinity of the representative cross section C. This shows that the cross section corresponding to the position of this marker is currently displayed in the continuous tomographic image 72. As the cross sections are sequentially displayed, the white triangular markers are represented by the representative cross section B and the representative cross section D. The display is moved along the circumference.

  FIG. 9 is a flowchart for explaining manual trace processing in the present embodiment. The flowchart of FIG. 9 corresponds to the specific processing content in S106 of FIG.

  When n reference cross sections (representative cross sections) are displayed as tomographic images on the screen in S105 of FIG. 2, in S901 of FIG. 9, for example, the user performs a manual trace while viewing the displayed tomographic images. Specify the cross section. Next, in S902, the user designates the start and end surfaces of a plurality of cross sections used for the continuous tomographic image (reference numeral 72 in FIG. 7) with the designated representative cross section as a reference.

  Specifically, for example, while viewing the index image 74 in FIG. 7, the user designates the start surface and the end surface by sliding the position of the filled triangular marker in the index image 74. The start surface and the end surface may be automatically set (default setting) to the representative cross sections (for example, the representative cross sections B and D) adjacent to the left and right sides of the designated representative cross section (for example, the representative cross section C). Incidentally, when the designated representative cross section is an end face (for example, the representative cross section A), the representative cross section itself is set as the start face, and the adjacent representative cross section (for example, the representative cross section B) is set as the end face.

  When the start surface and the end surface are designated, continuous display of the continuous tomographic image (reference numeral 72 in FIG. 7) is started in S903 of FIG. 9, and the continuous display is stopped in S904. The user confirms the boundary of the placenta (reference numeral 42B in FIG. 7) as the target tissue while viewing the continuous tomographic images continuously displayed between S903 and S904, and manually traces the boundary of the placenta in S905. In addition, you may perform a manual trace in the state which continued the continuous display, without stopping a continuous display.

  When the manual trace is executed, display of an image obtained by synthesizing the manual trace line 66 on the continuous tomographic image (reference numeral 72 in FIG. 7) is started in S906 of FIG. 9, and the display of the image is stopped in S907. . The user confirms whether or not the manual trace line is appropriate while looking at the continuous tomographic images continuously displayed between S906 and S907 and the manual trace line synthesized therewith.

  If the manual trace line is not appropriate, the process proceeds from S908 to S910, the manual trace line is corrected, the process returns to S906 again, and the corrected manual trace line is confirmed.

  If the manual trace line is appropriate, the manual trace is confirmed in S908, and the trace of the representative cross section designated in S901 is ended. Further, in S909, it is confirmed whether or not manual tracing has been completed for all the representative cross sections. If not completed, the process returns to S901 again, the remaining representative cross sections are designated, and the processing from S902 is executed again. The If it is confirmed in S909 that manual tracing has been completed for all representative cross sections, the flowchart of FIG. 9 ends, and the process proceeds to S107 of FIG.

  Returning to FIG. 2, in step S107, automatic correction processing of the manual trace line is executed. This correction process is performed for each manual trace line, that is, for each manual trace reference section as a representative section. For example, edge detection processing is performed on the periphery of each point on the manual trace line, and position correction processing for shifting the point to a position on the edge is performed on the point where the edge is detected. However, if no edge is detected, the manual trace result is stored as it is. Thereby, for example, the line portion 66A on the amniotic fluid 45 side shown in FIG. 6 is corrected to the automatic trace line portion faithfully traced along the contour 42C, while the luminance difference is not so much on the portion on the uterus 43 side. Since there is no automatic trace, the original shape is stored as the manual trace line portion 68B.

  In S108 of FIG. 2, the automatic trace processing is executed for the plurality of reference sections 60 for automatic trace shown in FIG. In this case, as shown in FIG. 10, composite trace lines as a plurality of corrected manual trace lines formed on a plurality of reference cross sections 58 for manual trace are used as a reference, and interpolation processing is performed based on them. By doing so, the trace surface 72 is configured by connecting a plurality of closed loops in a planar shape. In this case, it is not necessary to define a complete three-dimensional curved surface, but the interpolation processing is executed so that a complementary trace line can be defined at least for each automatic trace reference section 60.

  In S109 of FIG. 2, a process for correcting the complementary trace line of the reference section for automatic tracing is executed. Specifically, similar to the processing in S107, the automatic trace correction processing is performed on the line portion in contact with the amniotic fluid, while the trace result by complementation is stored and respected as it is in the portion in contact with the uterus. And the interpolated trace lines are partially modified. Such a process is executed for each reference section for automatic tracing.

  When the above processing is performed, as shown in FIG. 10, it is possible to define the automatically corrected trace surface 72 that wraps the entire placenta as the target tissue along its form. Consists of a plurality of closed loops, ie, a plurality of trace lines. These trace lines are composed of the above-described plurality of composite trace lines (manual trace lines after automatic correction) and a plurality of automatic trace lines after automatic correction.

  Therefore, in S110 of FIG. 2, the volume calculation unit (reference numeral 24 in FIG. 1) obtains the volume of the placenta based on the Disk Summation method or the like. That is, as shown in FIG. 10, since a plurality of trace lines as closed loops are formed throughout the placenta, the placenta volume is approximately obtained based on these trace lines. In that case, the distance between each closed loop, that is, between each cross section is also used.

  The calculated volume value data is sent to the display image forming unit (reference numeral 26 in FIG. 1). In S111 in FIG. 2, the extracted three-dimensional image of the tissue is displayed, and the calculated volume value is displayed on the screen. Displayed above.

  In the above embodiment, setting of the reference cross section, designation of both end points, designation of the number of representative cross sections, the number of the entire cross section set, and the like have been set by the user, but all or part of them are automatically set. You may make it set. Further, these values may be automatically changed according to the situation. In the above embodiment, the plurality of cross-sections are basically set at equal intervals. For example, for a site where the morphological change of the tissue is severe, the cross-section interval is reduced, that is, the cross-section is set densely, and the others. In this part, the interval between the cross sections may be increased, that is, the cross section may be set roughly. In addition, various methods proposed in the past can be applied as the automatic trace and trace line correction methods.

  As mentioned above, although preferred embodiment of this invention was described, embodiment mentioned above is only a mere illustration in all the points, and does not limit the scope of the present invention. The present invention includes various modifications without departing from the essence thereof.

1 is a block diagram showing an embodiment of an ultrasonic diagnostic apparatus according to the present invention. It is a flowchart for demonstrating the extraction process of object organization. It is a figure for demonstrating the setting of the reference | standard cross section with respect to volume data. It is a figure for demonstrating the setting of the reference line on a tomographic image. It is a figure which shows the reference cross-section row | line formed with respect to volume data. It is a figure for demonstrating a manual trace line. It is a figure which shows the example 1 of a display image displayed in the case of a manual trace. It is a figure which shows the example 2 of a display image displayed in the case of a manual trace. It is a flowchart for demonstrating a manual trace process. It is a figure which shows the trace surface which consists of a some trace line.

Explanation of symbols

  10 3D probe, 12 transmitting unit, 14 receiving unit, 16 3D data memory, 18 three-dimensional image forming unit, 20 arbitrary tomographic image forming unit, 22 tissue extracting unit, 24 volume calculating unit, 26 display image forming unit.

Claims (6)

A data acquisition unit that obtains volume data by transmitting and receiving ultrasonic waves to and from a three-dimensional space including the target tissue;
In a virtual data space composed of volume data, a cross-section setting unit that sets a cross-section set composed of a plurality of cross sections for the target tissue,
A trace processing unit that sets a manual trace line corresponding to the contour of the target tissue in response to an input from the user with respect to the representative cross section included in the cross section set,
As an input support image for the input, a display processing unit that sequentially displays tomographic images of a plurality of cross sections arranged with reference to a representative cross section in a cross section set;
Having
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1,
The display processing unit synthesizes and displays the image of the manual trace line in a tomographic image sequentially displayed as the input support image.
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1,
The display processing unit displays a reference image representing an arrangement state of a plurality of cross sections constituting the cross section set, and a marker for specifying a position of a cross section currently displayed in the input support image is included in the reference image. indicate,
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 3.
The display processing unit displays a marker indicating an array range of a plurality of cross sections used in the input support image in the reference image.
An ultrasonic diagnostic apparatus. The ultrasonic diagnostic apparatus according to claim 1,
An array range of a plurality of cross sections used for the input support image and a display speed of tomographic images sequentially displayed as the input support image are variably set.
An ultrasonic diagnostic apparatus. A method for processing volume data obtained by transmitting and receiving ultrasonic waves to and from a three-dimensional space including a target tissue,
In a virtual data space composed of volume data, a section setting step for setting a section set composed of a plurality of sections for a target tissue,
A trace processing step for setting a manual trace line corresponding to the contour of the target tissue in response to an input from the user with respect to the representative cross section included in the cross section set,
As an input support image for the input, a display processing step for sequentially displaying tomographic images of a plurality of sections arranged with reference to a representative section in a section set;
including,
A data processing method.

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